High dose output, through transmission and relective target X-ray system and methods of use

ABSTRACT

A high dose output, through transmission and reflective target x-ray tube and methods of use includes, in general an x-ray tube for accelerating electrons under a high voltage potential having an evacuated high voltage housing, a hemispherical shaped through and reflective transmission target anode disposed in said housing, a cathode structure to deflect the electrons toward the hemispherical anode disposed in said housing, a filament located in the geometric center of the anode hemisphere disposed in said housing, a power supply connected to said cathode to provide accelerating voltage to the electrons.

CROSS REFERENCE TO RELATED APPLICATIONS

To the full extent permitted by law, the present United StatesNon-provisional patent application is a Continuation-in-Part of, herebyclaims priority to and the full benefit of U. S. Non-Provisional patentapplication entitled “High Dose Output, Through Transmission TargetX-Ray System and Methods of Use,” filed on Dec. 31, 2014, havingassigned Ser. No. 14/587,634.

TECHNICAL FIELD

The disclosure relates generally to x-ray tube technology and morespecifically it relates to x-ray tubes with specific anode, cathode,filament configurations and material choices to produce high dose x-rayoutput.

BACKGROUND

In many typical state of the art X-ray tubes, a cathode assembly and ananode assembly are vacuum sealed in a glass or metal envelope. Electronsare generated by at least one cathode filament in the cathode assembly.These electrons are accelerated toward the anode assembly by a highvoltage electrical field. The high energy electrons generate X-rays uponimpact with the anode assembly. A by-product of this process is thegeneration of substantial amounts of heat.

Traditional x-ray tube configurations are known in the prior art, forexample, Coolidge type X-ray tubes. In a Coolidge tube X-ray photons,shown as a spot output radiation pattern, are generated by impinging anelectron beam emanating from filament onto the surface of a targetanode. Coolidge tubes may be operated single ended with the cathode at anegative potential and the anode at ground, or double ended with thecathode at a negative potential and the anode at a positive potential.In either configuration the energy of acceleration is the differencebetween the electrode potentials. In a Coolidge X-ray tube the targetanode is fabricated from a heavy metal such as tungsten, tantalum oriridium and such materials are selected because of their density andhigh melting point. The material of the target anode is most oftenmounted onto a thermally conductive material such as copper and isexternally cooled either by water or dielectric oil.

The target anode is placed in line with the electron beam and radiationis emitted at right angles to the electron beam. The spectrum of theoutput radiation is predominantly bremsstrahlung and is altered bychanging the accelerating energy of the electron beam. Tubes of thisnature are use in industrial imaging, medical imaging, analytical andirradiation application. The primary limitation of this type of tube isthe watt density loading of the target anode before melting occurs,limited utilization of generated x-ray photons and the symmetry of theresulting radiation field. Because the resolution of an imaging device,either electronic or film, is a function of the size of the electronbeam projected onto the target anode. For optimal image resolution asmall focal spot is desired, but for optimal image contrast a largenumber of X-ray photons are desired. The two requirements are contraryand cannot be resolved in the traditional tube design. In addition thereflective nature of the emitted radiation is asymmetrical about a beamcenterline and is grossly inefficient for X-ray irradiationapplications.

Recently, some low power through transmission X-ray tubes have becomeavailable on the market. These tubes use a use a single element as acombination target and output window. Most often the element used isTungsten because of its higher melting point but at the expense of areduction in radiation output.

Therefore, it is readily apparent that there is a recognizable unmetneed for a high dose output, through transmission target x-ray systemand methods of use, having a large surface area anode target todissipate heat, and thus, enabling a higher atomic number targetmaterial with improved radiation output, lower melting point and highervaporization pressure, and low electrode potential required to producehigher output radiation.

BRIEF SUMMARY

Briefly described, in example embodiment, the present apparatusovercomes the above-mentioned disadvantage, and meets the recognizedneed for a high dose output, through transmission target x-ray tube andmethods of use including, in general, an x-ray tube for acceleratingelectrons under a high voltage potential, said x-ray tube includes anevacuated housing that is sealed, a through transmission target anodestructure disposed on said housing, said anode structure configured in ahemispherical shape having a geometric center, a cathode structuredisposed in said housing, said cathode configured to deflect theelectrons toward said hemispherical anode, a filament disposed in saidhousing, said filament positioned proximate said geometric center ofsaid hemispherical shape and between said anode and said cathode, anevacuated housing, said housing configured to vacuum seal there in saidanode, said cathode, and said filament, and, thus, such x-ray tubefunctions to provide a large surface area anode target to dissipate heatand to enable use of different z materials to take advantage of thecharacteristic x-ray with improved radiation output, lower meltingpoint, and lower electrode potential required to produce higher outputradiation.

According to its major aspects and broadly stated, the a high doseoutput, through transmission target x-ray tube and methods of useincludes, in general an x-ray tube for accelerating electrons under ahigh voltage potential having an evacuated high voltage housing, ahemispherical shaped through transmission target anode disposed in saidhousing, a cathode structure to deflect the electrons toward thehemispherical anode disposed in said housing, a filament located in thegeometric center of the anode hemisphere disposed in said housing, apower supply connected to said cathode to provide accelerating voltageto the electrons.

In an exemplary embodiment of through transmission target x-ray tube andmethods of use, the x-ray tube including an evacuated housing that issealed, a through transmission target anode structure disposed on thehousing, the anode structure configured in a hemispherical shape havinga geometric center, a cathode structure disposed in the housing, thecathode configured to deflect the electrons toward the anode structure,a filament disposed in the housing, the filament positioned proximatethe geometric center of the hemispherical shape and between the anodeand the cathode, wherein the evacuated housing is configured to vacuumseal therein the anode structure, the cathode structure, and thefilament.

In another exemplary embodiment of through transmission and reflectivetarget x-ray tube for accelerating electrons under a high voltagepotential, includes a housing, a through and reflective transmissiontarget anode structure disposed on the housing, the anode structureconfigured in a hemispherical shape having a center of a circle createdby a 2D base, a cathode structure disposed in the housing, the cathodestructure configured to deflect the electrons toward the anodestructure, a filament disposed in the housing, the filament positionedproximate the center of a circle created by a 2D base of thehemispherical shape and between the anode structure and the cathodestructure, wherein the evacuated housing is configured to vacuum sealtherein the anode structure, the cathode structure, and the filament.

In an exemplary embodiment of through transmission target x-ray tubemethod of use to produce a monochromatic output X-ray spectrum includesthe steps of

providing an X-ray tube for accelerating electrons under a high voltagepotential having an evacuated housing that is sealed, a through andreflective transmission target anode structure disposed on the housing,the anode structure configured in a hemispherical shape having ageometric center, a cathode structure disposed in the housing, thecathode structure is configured to deflect the electrons toward theanode structure, a filament disposed in the housing, the filamentpositioned proximate a center of a circle created by a 2D base of thehemispherical shape and between the anode structure and the cathodestructure, wherein the circle created by the 2D base of thehemispherical shape is in direct contact with the cathode structure, andwherein the evacuated housing is configured to vacuum seal therein theanode structure, the cathode structure, and the filament, filtering theoutput X-ray spectrum just below a K alpha energy of the at least onetarget element, and adjusting the cathode voltage just above the K alphaenergy of the at least one target element.

Accordingly, a feature of the high dose output, through transmissiontarget x-ray tube and methods of use is its ability to generatesymmetrical x-ray field.

Another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide large surfacearea anode target to dissipate heat.

Still another feature of the high dose output, through transmissiontarget x-ray tube and methods of use is its ability to enable use of adifferent z material to take advantage of the characteristic x-ray whichwill increase radiation output.

Still another feature of the high dose output, through transmissiontarget x-ray tube and methods of use is its ability to use targetmaterials with lower melting points for specialized applications such asthe generation of monochromatic x-rays and for therapeutic applications.

Still another feature of the high dose output, through transmissiontarget x-ray tube and methods of use is its ability to utilize a lowerelectrode potential to produce higher output radiation.

Yet another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide a new anodeconfiguration which makes possible the use of alternate target materialshaving different characteristic x-rays.

Yet another feature the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide x-ray tube thatrequires no or limited heat dissipation in the form of air cooling orliquid cooling. Moreover, forced air cooling is thus more effectivebecause of the increased surface area of the new anode configuration.

Yet another feature the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide an x-ray tubewith increased longevity due to the large surface area anode targetability to dissipate heat.

Yet another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide a new structureand geometry for the anode to increase the surface area of the anode.

Yet another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide an anodeconfiguration with better heat transfer characteristics which wouldenable the anode to operate at a lower temperature, and thus enable alower melting point material choice with improved radiation output andextend the operational life of the X-ray tube.

Yet another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide a new structureand geometry for the cathode which deflects and/or accelerates theelectrons toward a new structure and geometry for the anode.

Yet another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide a new structureand geometry for the filament which releases the electrons evenlydistributed toward the a new structure and geometry for the anode.

Yet another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to provide minimal anodetarget to radiation sample distance resulting in an X-ray source whichcan be placed closer to a subject.

Yet another feature of the high dose output, through transmission targetx-ray tube and methods of use is its ability to produces X-rays used forbiological or organic material radiation, radiation treatment, treatingcertain diseases by killing or altering human cells, imaging, such asmedical, industrial, and dual energy, non-destructive evaluation ofobjects, X-ray defection, x-ray diffraction patterns, therapeutic X-ray,analytical x-ray, and x-ray microscopy.

Yet another feature of the high dose output, through transmission &reflective target x-ray tube and methods of use is its ability toproduce a useful amount of reflective photons in the opposite fromforward electron travel of the target anode. This phenomenon canobserved from a Z axis plot of the X-ray field.

Yet another feature of the high dose output, through transmission &reflective target x-ray tube and methods of use, because of thehemispherical shape of the anode and the corresponding cathodestructure, is the ability to passively manipulate the electron field bychanging the distance between the two structures.

Yet another feature of the high dose output, through transmission &reflective target x-ray tube and methods of use is the ability to changefilament size and shape to alter the electron emitting characteristics.

These and other features of high dose output, through transmission &reflective target x-ray tube and methods of use will become moreapparent to one skilled in the art from the following DetailedDescription of the exemplary Embodiments and Claims when read in lightof the accompanying drawing Figures.

BRIEF DESCRIPTION OF THE DRAWINGS

The present high dose output, through transmission target x-ray tube andmethods of use will be better understood by reading the DetailedDescription of the exemplary embodiments with reference to theaccompanying drawing figures, in which like reference numerals denotesimilar structure and refer to like elements throughout, and in which:

FIG. 1 is a schematic, cross sectional representation of a Coolidge typeprior art x-ray tube;

FIG. 2 is a schematic, cross sectional representation of an exemplaryembodiment of a through transmission target x-ray tube showing a profileof electron trajectory lines which are being emitted from the cathodefilament and showing a profile of the output radiation being emittedfrom the anode target;

FIG. 3 is a graphical representation of the x-ray energy keV verses thedose for gold target;

FIG. 3.1 is a graphical representation of the x-ray energy keV versesthe dose for a combination of materials such as Tungsten, Iridium, andGold as the target;

FIG. 4 is a graphical representation of the target anode thicknessverses dose for different kV;

FIG. 5 is a diagram representation of an example application to radiatebiological material utilizing the through transmission target x-ray tubeof FIG. 2;

FIG. 6 is a schematic, elevational, cross sectional representation of anexemplary embodiment of the through transmission target x-ray tube ofFIG. 2 in combination with a monochromatic filter;

FIG. 7 is a graphical representation of the x-ray energy verses the dosethe through transmission target x-ray tube in combination with amonochromatic filter of FIG. 6;

FIG. 8 is a schematic, elevational, cross sectional representation of analternate exemplary embodiment of through transmission target x-ray tubeshowing a profile of electron trajectory lines which are being emittedfrom the cathode filament and showing a profile of the output radiationbeing emitted from the anode target;

FIG. 9 is a flow diagram of a method of generating symmetrical shapedX-ray field;

FIG. 10 is a schematic, cross sectional representation of an alternateexemplary embodiment of a through transmission and reflective targetx-ray tube showing a profile of electron trajectory lines which arebeing emitted from the cathode filament and showing a profile of theoutput radiation being emitted from the anode target and reflected fromthe anode target;

FIG. 11A is a cross sectional representation of the alternate exemplaryembodiment of a through transmission and reflective target x-ray tube ofFIG. 10, shown with an extended tube sidewall;

FIG. 11B is a cross sectional representation of the alternate exemplaryembodiment of a through transmission and reflective target x-ray tube ofFIG. 10, shown with a shortened tube sidewall;

FIG. 12 is a cross sectional representation of the alternate exemplaryembodiment of a through transmission and reflective target x-ray tube ofFIG. 10 and a graphical representation of the photon intensity ofphotons or radiation in relation to tube centerline; and

FIG. 13 is a diagram representation of an example application to radiatebiological material utilizing the through transmission and reflectedtarget x-ray tube of FIG. 10.

It is to be noted that the drawings presented are intended solely forthe purpose of illustration and that they are, therefore, neitherdesired nor intended to limit the disclosure to any or all of the exactdetails of construction shown, except insofar as they may be deemedessential to the claimed invention.

DETAILED DESCRIPTION

In describing the exemplary embodiments of the present disclosure, asillustrated in FIGS. 1-3, 3.1, 4-10, 11A, 11B, 12-13 specificterminology is employed for the sake of clarity. The present disclosure,however, is not intended to be limited to the specific terminology soselected, and it is to be understood that each specific element includesall technical equivalents that operate in a similar manner to accomplishsimilar functions. The examples set forth herein are non-limitingexamples, and are merely examples among other possible examples.

Referring now to FIG. 1 there is illustrated a schematic cross sectionalrepresentation of Coolidge type X-ray tubes 12, shown in FIG. 1,includes x-ray tube housing 1, which may be glass or metal, high voltageinsulation 2, and a vacuum dielectric 3 contained therein x-ray tubehousing 1. In a Coolidge tube X-ray photons, shown as a fanned outputradiation pattern 7, are generated by impinging an electron beamemanating from filament 5, shown as electron trajectory 6 onto thesurface of a target anode 9, shown as x-ray target 9. Coolidge tubes maybe operated single ended with the cathode, shown as cathode assembly 4,at a negative potential and anode 9 at ground, or double ended with thecathode 4 at a negative potential and the anode 9 at a positivepotential. In either configuration the energy of acceleration is thedifference between the electrode potentials. In a Coolidge tube X-raythe target anode 9 is fabricated from a heavy metal such as tungsten,tantalum or iridium and such materials are selected because of theirdensity (tungsten-19.35, tantalum-16.65 or iridium-22.4 gr/cm3 (gramsper cubic centimeter)) and high melting point (tungsten-3410,tantalum-2996 or iridium-2410 Celsius (C)). The material of the targetanode 9 is most often mounted onto a thermally conductive material suchas copper, shown as anode heat conductor 8. Furthermore in Coolidge typeX-ray tubes 12 designs the amount of electrical energy between theelectrode potentials to produce a given resulting radiation 7 is veryhigh, resulting in heating of the target anode 9 material requiringspecial target cooling considerations such as a rotating target anode 9,air cooling or liquid cooling of the target anode 9, such as either bywater or a dielectric oil flowing through cooling lines 10. Theobjective of cooling the anode assembly is to enable higher poweroperation of the x-ray tube.

Moreover, the target anode 9 is placed in line with the electron beam 6and the resulting radiation 7 is emitted at right angles to the electronbeam 6 through output radiation window 11 forming a beam of outputradiation 7.

Referring now to FIG. 2, by way of example, and not limitation, there isillustrated schematic cross sectional representation of an exemplaryembodiment of high dose output, through transmission target x-ray tube20. Preferably, through transmission target x-ray tube 20 includesevacuated sealed chamber or envelope, such as housing 21, which may beglass, alloy or metal, which creates evacuated space 25. One end, afirst end 21.1 of housing 21 is preferably connected to first connector31 of high voltage power supply 33. Contained within housing 21preferably are primary elements anode structure 22, cathode structure23, first filament lead 27, second filament leads 28, and filament 24.Moreover, anode structure 22 preferably includes through transmissiontarget 43 anode as part of anode structure 22, where target 43 ispreferably deposited thereon inner surface 42 of first end 21.1 ofhousing 21. Cathode structure 23 may be connected to ground or secondconnector 32 of high voltage power supply 33. Filament 24 preferably isconnected to first filament lead 27 of heating current power supply 44and second filament leads 28 of heating current power supply 44.Preferably target 43 being the electron interacting material depositedthereon inner surface 42 of first end 21.1 of housing 21 and togetherwith arcing or circular cross-sectional, dome or hemispherical shapedfirst end 21.1 of housing 21 comprise anode structure 22. Yet stillfurther contained within housing 21 preferably is high voltage insulator26 partially enclosed housing 21 thereon second end 21.2 of housing 21.

Bremsstrahlung and characteristic radiation 30 is preferably emittedfrom through transmission target x-ray tube 20 in arcing or halfcircular cross-sectional, dome or hemispherical shape radiation pattern.Characteristic radiation is produced when an energetic electron emanatesfrom heated filament 24 and is accelerated by high voltage power supply33, the electrical energy between the electrode potentials of anodestructure 22 and cathode structure 23 onto the surface of target anodestructure 22, shown as electron trajectory 35, knocks an electron fromtarget element, target 43, out of its orbit. When this occurs anelectron in the next higher energy orbit will fall into this lowerenergy orbit and give off a burst of radiation equivalent to the energydifference between the two electron orbits. Because each element ormaterial of target 43, has a different atomic structure, energy level ofthe emitted radiation is unique and characteristic of that element. Theatomic levels are designated K, L, M, N . . . and each level hasadditional sub-levels designated α, β . . . . For example, if there is avacancy in the K-orbit of an element, target 43, and an electron dropsfrom the L orbit to fill the vacancy then the energy given off is equalto E_(X-ray)=E_(kα)−E_(L). The predominated and most usefulcharacteristic radiation is the K_(α) energy level of the variouselements, target 43, and occur at energies less than 100 kilovolts (kV)for high voltage power supply 33, the electrical energy between theelectrode potentials of anode structure 22 and cathode structure 23. Itis recognized herein that through transmission target x-ray tube 20preferably may use the Kα characteristic radiation of target 43 or acomposite target 43 composed of various elements to fill in the X-rayspectrum below 100 kilovolts (kV) and bremsstrahlung from higher Zelements to produce an X-ray tube of superior performancecharacteristics.

TABLE I target 43 material or combination materials Anode BremsstrahlungCharacteristic Total Material(43) Radiation Radiation Radiation Tungsten700 300 1000 Tungsten + Gold 700 600 1300 Tungsten + Gold + Iridium 700900 1600 All readings normalized for a Tungsten anode and operation at200 kV.

A New Housing and Target Anode Structure Shape

To address the shortcomings of traditional X-ray tubes and currentthrough transmission tubes through transmission target x-ray tube 20with selective anode structure 22 elements has been designed.Preferably, through transmission target x-ray tube 20 utilizes a largediameter 52, hemispherical shaped structure for anode structure 22 ofhousing 21 formed of a low Z material, such as aluminum or beryllium,carbon, ceramic, stainless steel, or alloys thereof, for a substrateonto which various target 43 elements or material may be deposited toform anode structure 22 (one target element is formed thereon the anodestructure via one of electro-chemically platted plating, mechanicallybonding, or vapor deposition using evaporation or sputtering technique).A hemispherically shaped anode structure 22 is preferably used becauseit has twice the surface area of a disk shaped substrate of the samediameter. The area of a hemisphere is 2πr² and the area of a disk isπr². This increase in surface area allows for increased powerdissipation, improved electron symmetry across target 43, increasedsurface area to dissipate heat, and thus, improved cooling efficiency.Moreover, the anode substrate 22 may be coated with various elements,combination of elements or their alloys as target 43 to form anodestructure 22 and produce desirable characteristic radiation 30 forspecific purposes or high Z elements to produce increased output with acombination of bremsstrahlung and characteristic radiation 30. This isall accomplished at reduced cathode potential, high voltage power supply33, for the same radiation 30 output as compared to a Coolidge typeX-ray tube, shown in FIG. 1.

It is recognized herein that the hemispherical shaped anode structure 22configured with a large surface area results in a self-cooled or cooleror lower temperature anode due to its ability to dissipate heat across alarger surface area, and thus, does not require any internal coolingsystem, such as rotating anode or cooling fluids with internal passages,to dissipate the heat generated in anode structure 22 during operation.

It is further recognized herein that the hemispherical shaped anodestructure 22 configured with a large surface area provides equalizeddistribution of electrons symmetrically across anode structure 22 andthus, generates an even distribution of radiation 30.

Specifically Coated Target Anode Substrate

Preferably, through transmission target x-ray tube 20 utilizes Gold astarget 43 coated hemispherical anode structure 22 deposited on innersurface 42 of first end 21.1 of housing 21 to form anode structure 22.Gold as target 43 element of anode structure 22 has a Kα peak atapproximately 68.8 keV and K_(β) peak at approximately 77 keV whenoperated at 150 to 160 kilovolts (kV), high voltage power supply 33, thebremsstrahlung and characteristic radiation spectrum, radiation 30, asshown in FIG. 3, is ideally suited for high output irradiationapplication(s) and is far superior to traditional X-ray tubes, such asCoolidge type X-ray tube, shown in FIG. 1. because of the followingadvantages. Preferably Gold target 43 element of anode structure 22provides the following advantages due to the efficiency of radiation 30produce is proportional to the atomic number of Gold target 43 of anodestructure 22 multiplied by the kV of high voltage power supply 33. Here,the atomic number of Gold (Au) is 79 the atomic number of Tungsten (W)is 74 for Coolidge type X-ray tube, shown in FIG. 1. The percentdifference between the two atomic numbers is 6.75%. Based on formula forcalculating radiation 30 1−((kV*z)/(kV*z))*100=Efficiency kV*Z*10-6;Gold utilized as target anode structure 22 is 6.75% more efficient ingenerating bremsstrahlung radiation, radiation 30, at the same kilovolts(kV) levels as Tungsten (W) targets 43 for Coolidge type X-ray tube,shown in FIG. 1. Traditional X-ray tubes cannot take advantage of usingGold as target 43 material for high power irradiation tubes because ofthe lower melting temperature of Gold (1064 Celsius) compared withTungsten (3422 Celsius) due to the small surface area design of anode 8of Coolidge type X-ray tube, shown in FIG. 1. However, with the largertarget 43 area provided for by hemispherical shaped structure of anodestructure 22 of through transmission target x-ray tube 20 the anodesurface area 22 is increased allowing for increased power dissipation;and therefore, lower melting point elements, such as Gold, may beutilized for target 43. For example, anode structure 22 area can be aslarge as 25 square inches compared to 1 square inch for anode 9 of FIG.1 which may operate at 1 Mega W/cm². It is contemplated herein thatother lower melting point elements for target 43, such as elements withatomic number between 74 through 82, and more specifically Lead (Pb) andUranium (U) and the like may be utilized as target 43 material for anodestructure 22. It is further contemplated herein that between 4-40microns thickness for target 43 material for anode structure 22 ispreferred and the thickness of target 43 material is chosen depending onthe material selected for target 43, desired type of radiation 30emission, and the accelerating voltage of high voltage power supply 33.These characteristics enable mono chromatic beams with increasedradiation at lower kV of high voltage power supply 33.

Target 43 is preferably formed of a suitable material, such as gold (Au)or Lead (Pb), including other elements with atomic number between 74through 82, and additionally copper (Cu), silver (Ag), and Uranium (U)may be utilized for target anode structure 22. Preferably, thesematerials include other suitable characteristics, such as high K_(α)energy level, high conversion rate of electrons to x-ray or otherbeneficial characteristic understood by one skilled in the art.

Furthermore, filament 24 of through transmission target x-ray tube 20 ispreferably configured in an arcing or circular cross-sectional orhemispherical shaped configuration, positioned therein cathode structure23 and such configuration electrostatically focuses electron beam 29along electron trajectory 35 toward anode structure 22 or morespecifically in a one-hundred and eighty degree (180°) or hemisphericalshaped pattern onto target 43 of anode structure 22 to evenly distributeelectron beam 29 across target 43, inner surface 42 of first end 21.1 ofanode structure 22 of housing 21. Moreover filament 24 is preferablycoated with an oxide material approximately 40-50 microns thick andindirectly heated using a nicon wire connected to first filament lead 27of heating current power supply 44 and second filament leads 28 ofheating current power supply 44 to heat filament 24 to provide thermalvibration energy to free electrons from filament 24. Such distributionof electron beam 29 across target 43 and anode structure 22 lowers orreduces the watt density (Watts/Area, W/cm²) loading of target 43 andanode structure 22, as set forth above, and, thus prevents hot spots dueto even heating of target 43 and anode structure 22.

It is recognized herein that the hemispherical shaped anode structure 22and arcing or hemispherical shaped filament 24, in combination, providesequalized distribution of electrons symmetrically across target 43 andanode structure 22.

It is further recognized herein that the hemispherical shaped anodestructure 22 and arcing or hemispherical shaped filament 24, incombination, provides collimating electron trajectory 35 across target43 and anode structure 22.

It is further recognized herein that the hemispherical shaped anodestructure 22 and arcing or hemispherical shaped filament 24, incombination, provides equalized electron travel distance 58, thedistance electron beam 29 travels from filament 24 to target anodestructure 22.

Still furthermore, cathode structure 23 of through transmission targetx-ray tube 20 is preferably configured in an ‘V’ shape or notched ‘V’shape cross-section, or bowl or flared configuration or the like andsuch configuration electrostatically directs electron beam 29efficiently and equally distributed along electron trajectory 35 towardtarget 43 and anode structure 22 or more specifically in a one-hundredand eighty degree (180°) pattern onto target 43 and anode structure 22to evenly distribute electron beam 29 across hemispherically shapedtarget 43 and anode structure 22, inner surface 42 of first end 21.1 ofhousing 21.

It is recognized herein that the hemispherical shaped anode structure22, arcing or hemispherical shaped filament 24, and flared cathodestructure 23 in combination, provides maximum generation of directionalx-rays proximately symmetrical about center line CL.

It is recognized herein that the transmission type x-ray tube 20 targetmay include an anode structure having a specifically coated target 43,such as by using parameters of target 43 material.

It is recognized herein that through transmission target x-ray tube 20may include a specifically coated target 43 of anode structure 22 forX-ray defection, such as by using low Z materials for target 43.

It is recognized herein that through transmission target x-ray tube 20may include a specifically coated target 43 of anode structure 22 forX-ray deflection, such as by using high Z materials for target 43.

It is recognized herein that through transmission target x-ray tube 20may include a specifically coated target 43 of anode structure 22 forlow power requirements of high voltage power supply 33, or for high doseradiation 30 application, such as by using parameters of the target 43material.

It is recognized herein that through transmission target x-ray tube 20may include a specifically coated target 43 of anode structure 22 formedical imaging, such as by using Molybdenum as target 43 material.

It is recognized herein that through transmission target x-ray tube 20may include a specifically coated target 43 of anode structure 22 forindustrial imaging, such as by using Gold as the target material 43 toincrease the number of X-ray photons which in turn improves imagecontrast.

Referring now to FIG. 3, by way of example, and not limitation, there isillustrated graphical representation of the x-ray energy keV(λ) versesoutput radiation dose for through transmission target x-ray tube 20,shown having target 43 material of Gold. In this graph of thecharacteristic radiation R1 of target 43 material of Gold the Y axisrepresents dose a given quantity of output radiation, radiation 30, inphotons, such as number of photons and the X axis represents Kilovolts(wavelength) a given quantity of x-ray energy, and as Kilovolts(wavelength) changes so does the number of photons dose represented bythe graph for Gold. As seen in the graph radiation spikes occur and aredesignated as K_(α) and K_(β) dose peaks, which are characteristicradiation peaks that results from using target 43 material of Gold.Using target 43 material of Gold results in increases in radiation doseoccur for target 43 material without requiring increased input powerkV(λ), due to radiation spikes shown as proximately kV(λ) of 68.7corresponding to K_(α) peak and kV(λ) of 77 corresponding to K_(β) peak.

Referring now to FIG. 3.1, by way of example, and not limitation, thereis illustrated graphical representation of the x-ray energy kV(λ) versesoutput radiation dose for through transmission target x-ray tube 20,shown having target 43 material of configured based on a combination ofmaterials for target 43. Preferably target 43 is preferably formed of asuitable material, such as gold (Au), Lead (Pb), including otherelements with atomic number between 74 through 82, and additionallycopper (Cu), silver (Ag), and Uranium (U). In this graph of thecharacteristic radiation R2 of combination target 43 of Gold Tungstenand Iridium the Y axis represents dose a given quantity of radiation inphotons, such as number of photons and the X axis represents Kilovolts(wavelength) a given quantity of x-ray energy, and as Kilovolts(wavelength) changes so does the number of photons dose. As seen in thegraph radiation spikes occur and are designated as K_(α) and K_(β) peaksfor both Gold Tungsten and Iridium, which are characteristic radiationpeaks that results from using combination of materials for target 43.Using target 43 material of Gold Tungsten and Iridium results inincreases in output radiation dose, radiation 30, which occur forcombination material, target 43 without requiring increased input powerkV(λ) high voltage power supply 33, as shown in Table II

TABLE II Element K_(α)1 K_(α)2 K_(β)1 K_(β)2 Gold 68.804 66.990 77.98580.182 Tungsten 59.318 57.982 67.244 69.1 Iridium 64.896 63.287 73.56075.620

It is recognized herein that for each material selected from the elementlist above to make up combination material, for target 43, as shown thecharacteristic radiation R2 of target 43 will have additional anddifferent K_(α) and K_(β), peaks for each material selected and added totarget 43. It is further recognized herein that the addition of eachmaterial selected from the list above results in target 43 materialbased on a plurality of materials and each material generates additionaland different K_(α) and K_(β), peaks, and thus increases in outputradiation dose, radiation 30, occur for combination material, target 43without requiring increased input power kV(λ), high voltage power supply33, as shown by the increase in area of the graph of the characteristicradiation R2. By adding a plurality of combination material listed abovefor target 43 the improved output radiation dose, radiation 30,occurring for combination material target 43 will be greatly increased.If 1000 watts of power generates a dose of 100 Gray then a combinationtarget 43 may generate 50% more dose.

It is still further recognized that increases in output radiation dose,radiation 30, for target 43 material based on the above list ofmaterials without requiring increased input power (kV(λ)*mA) reducescooling requirements.

It is still further recognized that increases in output radiation dose,radiation 30, for target 43 material based on the above list ofmaterials without requiring increased input power (kV(λ)*mA), highvoltage power supply 33, enables radiation and irradiation applicationsat lower input power (kV(λ)*mA), such as medical applications.

Referring now to FIG. 4, by way of example, and not limitation, there isillustrated a graphical representation of the target 43 materialempirically determined thickness verses dose output radiation, radiation30, for through transmission target x-ray tube 20. In this graph of theBremsstrahlung radiation of target 43 verses material thickness the Yaxis represents dose a given quantity of output radiation, radiation 30,in photons, such as number of photons and the X axis represents target43 material thickness in micrometers, and as target 43 materialthickness changes so does the number of photons represented by thegraph. Thee representative curves are presented for varying high voltagepower supply 33, the electrical energy between the electrode potentialsof anode structure 22 and cathode structure 23, such as 50 kV Ra, 100 kVRb, and 200 kV Rc. In each curve dose ramps up, plateaus, and tapers offbased on increased target 43 material thickness. It is recognized hereinFIG. 4 that approximately 4-40 microns thickness for target 43 materialfor target anode structure 22 is preferred, and more preferredapproximately 4-18 microns thickness for target 43 material for targetanode structure 22, and the thickness of target 43 material is chosendepending on the material selected, desired type of radiation 30emission, and the accelerating voltage of high voltage power supply 33.

It is further recognized herein FIG. 4 that the higher the acceleratingvoltage, high voltage power supply 33, the more efficient throughtransmission target x-ray tube 20 is at converting electrons emitted byfilament 24 into increased dose output radiation 30 to take advantage ofthe characteristic radiation peeks.

It is still further recognized herein FIG. 4 that no sharp points occurin the characteristic radiation R curves 50 kV Ra, 100 kV Rb, and 200 kVRc, and more specifically representative radiation R curve 50 kV Rahaving a plateau from approximately 3-5 microns thickness of target 43,representative radiation R curve 100 kV Rb having a plateau fromapproximately 7-10 microns thickness of target 43, representativeradiation R curve 200 kV Rc having a plateau from approximately 14-18microns thickness of target 43 and collectively representative radiationR curves 50 kV Ra, 100 kV Rb, and 200 kV Rc plateau from preferred 4-18microns thickness of target 43.

Design variables of through transmission target x-ray tube 20, such asmaterial to be selected for target 43 (material having Z from 73 to 79heavier elements), selected target 43 material thickness in microns, andselected voltage of high voltage power supply 33 changes the dose outputradiation 30, such as increased dose output radiation at lower highvoltage power supply 33 power.

It is still further recognized herein FIG. 4 that changes to selectedtarget 43 material and/or selected target 43 material thickness inmicrons changes dose output radiation 30.

It is still further recognized herein FIG. 4 that dual energy throughtransmission target x-ray tube 20 having high voltage power supply 33operational at two voltages of for example 50 kV and 100 kV, maypreferably select target 43 material thickness to accommodate bothenergies, for example, target 43 material thickness of between 3-10microns may be selected where representative radiation R curve 50 kV Rahaving plateau from approximately 3-5 microns thickness of target 43 (50kV) and representative radiation R curve 100 kV Rb having plateau fromapproximately 7-10 microns thickness of target 43 (100 kV) overlap.

Referring now to FIG. 5, by way of example, and not limitation, there isillustrated an example application to radiate biological materialutilizing through transmission target x-ray tube 20, as shown anddescribed in FIG. 2. In use, through transmission target x-ray tube 20characteristic and Bremsstrahlung radiation 30 is preferably emittedfrom through transmission target x-ray tube 20 in arcing or halfcircular cross-sectional, dome or hemispherical shape radiation 30pattern. Preferably, through transmission target x-ray tube 20 producescharacteristic radiation 30 configured to enable a large area of intenseradiation 30 to improve throughput radiation and radiate more or anincreased number of samples S simultaneously. Furthermore, samples S maybe positioned proximate or adjacent anode structure 22 of housing 21 ofthrough transmission target x-ray tube 20, either positioned stationaryor via a mobile mechanical structure depending on the application for anadded level of even exposure of samples S subjected to characteristicradiation 30 by taking advantage of the geometrical shape of theradiation pattern. Moreover, through transmission target x-ray tube 20preferably produces a symmetrical radiation field, radiation 30, aroundfirst end 21.1 of through transmission target x-ray tube 20 to provide aconsistent dose of radiation 30 to all areas of samples S.

It is recognized herein that through transmission target x-ray tube 20radiation 30 output is increased over Coolidge type prior art x-raytube, shown in FIG. 1. For example, if two times radiation 30 outputfrom through transmission target x-ray tube 20 then samples S requirehalf the necessary runtime of through transmission target x-ray tube 20,and additionally higher dose radiation 30 using less power requirementsfor high voltage power supply 33, lowered heat load in BTU of airconditioning load savings with lowered power requirements, high voltagepower supply 33, all results in lowered operating costs of throughtransmission target x-ray tube 20. Moreover, hemispherical shaped anodestructure 22 configured with a large surface area results in a cooled orcooler or lower temperature anode due to its ability to dissipate heat,and thus, does not require any internal or external cooling system, suchas rotating anode or cooling fluids with internal passages, to dissipatethe heat generated in anode structure 22 during operation, and, thusreduces the operating cost of through transmission target x-ray tube 20.

Referring now to FIG. 6, by way of example, and not limitation, there isillustrated schematic cross sectional representation of high doseoutput, through transmission target x-ray tube 20 (alternatively 50) incombination with monochromatic filter 60. Preferably, monochromaticfilter 60 may be positioned proximate or adjacent first end 21.1 ofhousing 21 in the path of radiation 30 or between anode structure 22 ofhousing 21 and samples S in the path of radiation 30 to attenuate orfilter selected radiation from radiation 30. Referring again to FIG. 3by way of example, and not limitation, monochromatic filter 60 may beconfigured to filter or attenuate a specified radiation 30, such as allradiation less than kV(λ) of 54 to produce specified radiation 30 ofK_(α) and K_(β) dose peaks, which are characteristic radiation peaksthat results from using target 43 material of Gold.

FIG. 7 is a graphical representation of the x-ray energy verses the dosethe through transmission target x-ray tube 20 in combination with amonochromatic filter of FIG. 6. In this graph of the characteristicradiation R1 of target 43 material of Gold the Y axis represents dose agiven quantity of output radiation 30 in photons, such as number ofphotons and the X axis represents Kilovolts (wavelength) a givenquantity of x-ray energy, between kV(λ) of 75 and kV(λ) of 85, and asKilovolts (wavelength) changes so does the number of photons representedby dose radiation 30 for Gold. As seen in the graph radiation spikesoccur and are designated as K_(α) and K_(β) dose peaks, which arecharacteristic radiation peaks that results from using target 43material of Gold. In use, selected target 43 material and its K_(α) andK_(β) dose peaks along with selected monochromatic filter 60 preferablyenables a desired radiation profile for radiation 30, and, thus may bespecified to achieve a variety of specific radiation 30 profiles forthrough transmission target x-ray tube 20 (alternatively 50) forspecified imagery and therapy examples or uses.

Referring now to FIG. 8, by way of example, and not limitation, there isan illustrated schematic cross sectional representation of alternateexemplary embodiment of high dose output, through transmission targetx-ray tube 50. Preferably, through transmission target x-ray tube 50includes evacuated sealed chamber or envelope, such as housing 21, whichmay be glass, alloy or metal. One end, a first end 21.1 of housing 21 ispreferably connected to first connector 31 of high voltage power supply33. Contained within housing 21 preferably are primary elements anodestructure 22, cathode structure 23.1, first filament lead 27, secondfilament leads 28, and filament 24.1. Moreover, anode structure 22preferably includes through transmission target 43 anode as part ofanode structure 22, wherein target 43 is preferably deposited thereoninner surface 42 of first end 21.1 of housing 21. Cathode structure 23.1may be connected to ground or second connector 32 of high voltage powersupply 33. Filament 24.1 preferably is connected to first filament lead27 of heating current power supply 44 and second filament leads 28 ofheating current power supply 44. Target 43 being the electroninteracting material deposited (i.e., one target element is formedthereon the anode structure via one of electro-chemically plattedplating, mechanically bonding, or vapor deposition using evaporation orsputtering technique) thereon inner surface 42 of first end 21.1 ofhousing 21 and together with arcing or circular cross-sectional orhemispherical shaped first end 21.1 of housing 21 comprise anodestructure 22. Yet still further contained within housing 21 preferablyis high voltage insulator 26 partially enclosed housing 21 thereonsecond end 21.2 of housing 21.

Filament 24.1 of through transmission target x-ray tube 50 is preferablyconfigured in a straight linear or slightly curved cross-sectional orplanar or disc shaped configuration within cathode structure 23.1 andsuch configuration electrostatically focuses electron beam 29.1 alongelectron trajectory 35.1 toward target 43 and anode structure 22 or morespecifically in a focused spot configuration pattern onto target 43 andanode structure 22 to concentrate electron beam 29.1 proximate centerline CL across the inner surface 42 of first end 21.1 of housing 21.

Still furthermore, cathode structure 23.1 of through transmission targetx-ray tube 50 is preferably configured in an ‘U’ shape cross-section, orcylinder configuration or other focusing configuration and suchconfiguration electrostatically accelerate electron beam 29.1 alongelectron narrow trajectory 35.1 toward target 43 and anode structure 22or more specifically in a focused pattern onto target 43 and anodestructure 22 to narrowly distribute electron beam 29.1 acrosshemispherically shaped target 43 and anode structure 22, inner surface42 of first end 21.1 of housing 21. Such concentration of electron beam29.1 enables high dose output in narrow spot configuration having anodediameter 52, and through transmission target x-ray tube 50 may beutilized for applications, such as, to produce focused X-rays used for,radiation treatment, imaging, such as medical, industrial, and dualenergy, non-destructive evaluation of objects.

It is contemplated herein that spot diameter 52 may be scaled up/down orincreased or decreased in size based on design factors such as theopening or gap, such as inner diameter 56 of cathode structure 23.1,electron travel distance 58, of electron beam 29.1, the distance anelectron travels from filament 24.1 to target 43 and anode structure 22,and/or diameter 52 of hemispherical shaped anode structure 22 forhousing 21, as shown in FIG. 2. For example, in use, inner diameter 56of cathode structure 23.1, electron travel distance 58 of electron beam29.1 travels from filament 24.1 to target 43 and anode structure 22,and/or diameter 52 of hemispherical shaped anode structure 22 forhousing 21 may be specified to achieve spot diameter 52 proportional totumor sizes subject to radiation treatment depth of x-ray penetration.

It is recognized herein that the hemispherical shaped anode structure22, filament 24.1, and narrowed cathode structure 23.1 in combination,provide focused, radially linearly symmetric x-ray field.

It is recognized herein that the hemispherical shaped anode structure22, filament 24.1, and flared cathode structure 23.1 in combination,generate directional x-rays proximate center line CL for therapeuticx-ray treatment of melanoma and other cancer cells.

It is contemplated herein that monochromatic filter 60 may be utilizedwith through transmission target x-ray tube 50 similar to that shown anddisclosed in FIGS. 6 and 7.

Referring now to FIG. 9, by way of example, and not limitation, there isillustrated a flow diagram 900 of a method of generating symmetricalhemispherical shaped X-ray field. In block or step 910, providing highdose output, through transmission target x-ray tube 20/50 havingevacuated sealed housing 21, hemispherical shaped anode structure 22,cathode structure 23, target 43, and filament 24 as described herein. Inblock or step 915 selecting a material or combination of materials, zmaterial, for target 43. In block or step 920 selecting an acceleratingvoltage for high voltage power supply 33. In block or step 925 causingthe high dose output, through transmission target x-ray tube 20 toproduce x-rays for use in biological material radiation. In block orstep 930 causing the high dose output, through transmission target x-raytube 20 to produce x-rays for use in non-destructive evaluation of anobject. In block or step 935 causing the high dose output, throughtransmission target x-ray tube 20 to produce x-rays for use indestructive treatment of biological samples. Other treatments includeimaging, such as medical, industrial, and dual energy, non-destructiveevaluation of objects.

Referring now to FIG. 10, by way of example, and not limitation, thereis illustrated schematic cross sectional representation of alternateexemplary embodiment of high dose output, through transmission andreflective target x-ray tube 50. Preferably, through transmission andreflective target x-ray tube 50 includes evacuated sealed chamber orenvelope, such as housing 21, which may be glass, alloy or metal. Oneend, a first end 21.1 of housing 21 is preferably connected to firstconnector 31 of high voltage power supply 33. Contained within housing21 preferably are primary elements anode structure 22, cathode structure23.1, first filament lead 27, second filament leads 28, and filament24.1. Moreover, anode structure 22 preferably includes throughtransmission and reflective target 43 anode as part of anode structure22, wherein target 43 is preferably deposited thereon inner surface 42of first end 21.1 of housing 21. Cathode structure 23.1 may be connectedto ground or second connector 32 of high voltage power supply 33.Filament 24.1 preferably is connected to first filament lead 27 ofheating current power supply 44 and second filament leads 28 of heatingcurrent power supply 44. Target 43 being the electron interactingmaterial deposited thereon inner surface 42 of first end 21.1 of housing21 and together with arcing or circular cross-sectional 2-D circle orbase or hemispherical shaped first end 21.1 of housing 21 comprise anodestructure 22. Yet still further contained within housing 21 preferablyis high voltage insulator 26 partially enclosed housing 21 thereonsecond end 21.2 of housing 21.

Filament 24.1 of through transmission and reflective target x-ray tube50 is preferably configured in a straight linear or slightly curvedcross-sectional or planar or disc shaped configuration within cathodestructure 23.1 and such configuration electrostatically shapes electronbeam 29.1 along electron trajectory 35.1 toward target 43 and anodestructure 22 or more specifically in a large area electron pattern ontotarget 43 and anode structure 22 to equally distribute the electron beam29.1 proximate center line CL across the inner surface 42 of first end21.1 of housing 21. Moreover, filament 24.1 and cathode structure 23.1may be positioned proximate center line CL of arcing or circularcross-sectional 2-D circle or base or hemispherical shaped first end21.1 of housing 21 (center of a circle created by a 2D base ofhemispherical shaped first end 21.1) and between cathode structure 23.1.

Still furthermore, cathode structure 23.1 of through transmission andreflective target x-ray tube 50 is preferably or may be configured in an‘U’ shape cross-section, or cylinder configuration or other de-focusingconfiguration and such configuration electrostatically accelerateelectron beam 29.1 along electron trajectory 35.1 toward target 43 andanode structure 22 or more specifically in a de-focused pattern ontotarget 43 and anode structure 22 to equally distribute electron beam29.1 across hemispherically shaped target 43 and anode structure 22,inner surface 42 of first end 21.1 of housing 21. Such distribution ofelectron beam 29.1 enables high dose output in a pass through forwardphotons direction 52 (forward defined as same direction electrons ofelectron beam 29.1 are traveling in a fan-shaped pattern from anodestructure 22) and the utilization of reflective photons direction 52.1(reflective defined as the opposite direction electrons of electron beam29.1 are traveling in a reflective fan-shaped pattern from anodestructure 22) opposite the anode 22. In use, alternate exemplaryembodiment of high dose output, the through transmission and reflectivetarget x-ray tube 50 may be utilized for bulk irradiation of samples Svia through and reflective transmission target x-ray tube 50, such assymmetrical radiation field, radiation 30, around first end 21.1 ofthrough transmission target x-ray tube 50 to provide a consistent doseof radiation 30 to all areas of samples S positioned proximate first end21.1 of housing 21 as shown in FIG. 5; and alternatively radiationfield, radiation 30, around second end 21.2 of through transmissiontarget x-ray tube 50 to provide a consistent dose of radiation 30 to allareas of samples S positioned parallel to the centerline CL andproximate housing 21, and more specifically proximate second end 21.2 ofhousing 21 as shown in FIG. 13.

Referring now to FIG. 11A, by way of example, and not limitation, thereis illustrated cross sectional representation of alternate exemplaryembodiment of high dose output, through transmission and reflectivetarget x-ray tube 50A showing a reduced anode to cathode spacing.Preferably, alternate exemplary embodiment of high dose output, throughtransmission and reflective target x-ray tube 50A may be configuredhaving first end 21.1 of housing 21 or anode structure 22 positioned alinear distance 110A therefrom second end 21.2 of housing 21 or cathodestructure 23.1; wherein electron beam 29.1 enables high dose output in apass through forward photons direction 52A (forward defined as samedirection electrons of electron beam 29.1 are traveling in a broadfan-shaped pattern from anode structure 22) and the utilization ofreflective photons direction 52.1A (reflective defined as the oppositedirection electrons of electron beam 29.1 are traveling in a reflectivebroad fan-shaped pattern from anode structure 22) opposite the anode 22.

Referring now to FIG. 11B, by way of example, and not limitation, thereis illustrated cross sectional representation of alternate exemplaryembodiment of high dose output, through transmission and reflectivetarget x-ray tube 50B showing an increase in anode to cathode spacing.Preferably, alternate exemplary embodiment of high dose output, throughtransmission and reflective target x-ray tube 50B may be configuredhaving first end 21.1 of housing 21 or anode structure 22 positioned alinear distance 110B therefrom second end 21.2 of housing 21 or cathodestructure 23.1; wherein electron beam 29.1 enables high dose output in apass through forward photons direction 52B (forward defined as samedirection electrons of electron beam 29.1 are traveling in a narrowfan-shaped pattern from anode structure 22) and the utilization ofreflective photons direction 52.1B (reflective defined as the oppositedirection electrons of electron beam 29.1 are traveling in a reflectivenarrow ban pattern from anode structure 22) opposite the anode 22.

It is contemplated herein that spot diameter 52 may be scaled up/down orincreased/decreased in size of radiation 30, such as reflective photonsPr based on design factors, such as, the opening or gap, such as innercathode diameter 56 of cathode structure 23.1, electron travel distance58, of electron beam 29.1, the distance an electron travels fromfilament 24.1 to target 43, anode structure 22, and/or diameter 52 ofhemispherical shaped anode structure 22 for housing 21, as shown in FIG.2.

Referring now to FIGS. 11A, 11B, and 12, by way of example, and notlimitation, there is illustrated a graphical representation of thephoton intensity of pass through radiation 30, such as photons P(through transmission X-ray field or spectrum) and reflective radiation30, such as reflective photons Pr (reflective transmission X-ray fieldor spectrum) in relation to tube centerline Cl for through transmissiontarget x-ray tube 50. In this graph of the Normalized Number ofradiation 30, such as Photons P/Pr of through and reflectivetransmission target x-ray tube 50 verses distance in millimeters frombase line insulator 26 partially enclosed housing 21 thereon second end21.2 of housing 21. Moreover, referring again to FIG. 12, the Y axisrepresents Normalized Number of Photons P/Pr a given quantity of photonsP and reflective photons Pr in relation to tube centerline Cl forthrough transmission and reflective target x-ray tube 50 or outputradiation, radiation 30, in photons, such as number of photons and the Xaxis represents distance in millimeters from base line insulator 26partially enclosed housing 21 thereon second end 21.2 of housing 21. Inthis exemplary graph of FIG. 12, first end 21.1 of housing 21 or anodestructure 22 positioned a linear distance 110A may be approximatelytwo-hundred and seventy-five millimeters (275 mm) therefrom second end21.2 of housing 21 or cathode structure 23.1 and Normalized Number ofPhotons P/Pr ramps up, plateaus, and tapers off based on linear distance110A. It is recognized herein FIG. 12 that Normalized Number of PhotonsP/Pr ramps up at approximately seventy-five millimeters (75 mm),plateaus from at approximately seventy-five millimeters (75 mm) toapproximately two-hundred and fifty millimeters (250 mm), and ramps downthereafter two-hundred and fifty millimeters (250 mm).

It is contemplated herein that the design factors listed above may beutilized to vary or tune the position, location, quantity, and number ofpass through photons P and/or reflective photons Pr generated by throughtransmission and reflective target x-ray tube 50.

It is contemplated herein that the design factors, such linear distance110, such as first end 21.1 of housing 21 or anode structure 22positioned a linear distance 110 therefrom second end 21.2 of housing 21or cathode structure 23.1, and such adjustment, design or predeterminedlinear distance 110 varies the number and location of reflective photonsPr (reflective transmission X-ray field) generated by reflectivetransmission target x-ray tube 50, as set forth in FIGS. 11A, 11B, and12.

It is further recognized herein FIG. 12 that spot diameter 52 may bescaled up/down or increased or decreased in size of reflective photonsPr or side output radiation 30 based on design factors, such as, lineardistance 110A first end 21.1 of housing 21 or anode structure 22 andtherefrom second end 21.2 of housing 21 or cathode structure 23.1 aswell as the opening or gap, such as inner cathode diameter 56 of cathodestructure 23.1, electron travel distance 58, of electron beam 29.1, thedistance an electron travels from filament 24.1 to target 43, anodestructure 22, and/or diameter 52 of hemispherical shaped anode structure22 for housing 21, as shown in FIG. 2.

Referring now to FIG. 13, by way of example, and not limitation, thereis illustrated an example application to radiate biological materialutilizing through transmission target x-ray tube 50, as shown anddescribed in FIG. 10. In use, through transmission target x-ray tube 50characteristic and Bremsstrahlung radiation 30, P is preferably emittedfrom through transmission target x-ray tube 50 in arcing or halfcircular cross-sectional, dome or hemispherical shape radiation 30pattern (symmetrical hemispherical shaped reflective transmission x-rayfield) and reflected radiation 30, Pr is preferably reflected from anodestructure 22 for housing 21, as shown in FIG. 12. Preferably, throughand reflected transmission target x-ray tube 50 produces characteristicradiation 30 configured to enable a large area of intense radiation 30to improve throughput radiation and reflected radiation and radiate moreor an increased number of samples S simultaneously. Furthermore, samplesS may be positioned proximate, alongside, or adjacent anode structure 22of housing 21 of through transmission target x-ray tube 50, eitherpositioned stationary or via a mobile mechanical structure depending onthe application for an added level of even exposure of samples Ssubjected to characteristic radiation 30 (pass through photons P and/orreflective photons Pr) by taking advantage of the geometrical shape ofthe radiation pattern set forth in FIG. 12. Moreover, throughtransmission target x-ray tube 50 preferably produces a symmetricalradiation field, radiation 30 (pass through photons P and/or reflectivephotons Pr), around first end 21.1 and second end 21.2 of housing 21 ofthrough transmission target x-ray tube 50 to provide a consistent doseof radiation 30 to all areas of samples S.

It is recognized herein that through and reflective transmission targetx-ray tube 50 radiation 30 output is increased over Coolidge type priorart x-ray tube, shown in FIG. 1. For example, if two times radiation 30output from through transmission target x-ray tube 50 then samples Srequire half the necessary runtime of through transmission target x-raytube 50, and additionally higher dose radiation 30 using less powerrequirements for high voltage power supply 33, lowered heat load in BTUof air conditioning load savings with lowered power requirements, highvoltage power supply 33, all results in lowered operating costs ofthrough transmission target x-ray tube 50. Moreover, hemisphericalshaped anode structure 22 configured with a large surface area resultsin a cooled or cooler or lower temperature anode due to its ability todissipate heat, and thus, does not require any internal or externalcooling system, such as rotating anode or cooling fluids with internalpassages, to dissipate the heat generated in anode structure 22 duringoperation, and, thus reduces the operating cost of through transmissiontarget x-ray tube 50.

It is still further contemplated herein that through transmission andreflective target x-ray tube 50 radiation 30 may be utilized as abiological cell irradiator, virus deactivation irradiator, insectirradiator, blood irradiator, food irradiator.

The foregoing description and drawings comprise illustrative embodimentsof the present disclosure. Having thus described exemplary embodiments,it should be noted by those ordinarily skilled in the art that thewithin disclosures are exemplary only, and that various otheralternatives, adaptations, and modifications may be made within thescope of the present invention. Merely listing or numbering the steps ofa method in a certain order does not constitute any limitation on theorder of the steps of that method. Many modifications and otherembodiments of the invention will come to mind to one ordinarily skilledin the art to which this invention pertains having the benefit of theteachings presented in the foregoing descriptions and the associateddrawings. Although specific terms may be employed herein, they are usedin a generic and descriptive sense only and not for purposes oflimitation. Moreover, the present invention has been described indetail; it should be understood that various changes, substitutions andalterations can be made thereto without departing from the spirit andscope of the invention as defined by the appended claims. Accordingly,the present invention is not limited to the specific embodimentsillustrated herein, but is limited only by the following claims.

What is claimed is:
 1. An x-ray tube for accelerating electrons under ahigh voltage potential, the x-ray tube comprising: a housing; a targetanode structure disposed on said housing, said anode structureconfigured in a hemispherical shape having a center of a circle createdby a 2D base, wherein the anode structure disposed on the housing isformed of a low Z material, and wherein the target anode structure has atarget element coated thereon that has a thickness ranging between 2 and50 microns; a cathode structure disposed in said housing, wherein thecathode structure is configured to facilitate deflection of theelectrons along a trajectory toward said anode structure; a filamentdisposed in said housing, said filament positioned proximate said centerof a circle created by a 2D base of said hemispherical shape and betweensaid anode structure and said cathode structure, wherein said evacuatedhousing is configured to vacuum seal therein said anode structure, saidcathode structure, and said filament, wherein the low Z material of theanode structure, the thickness of the target element, and thehemispherical shape of the anode structure facilitate, based on theelectrons contacting the target element, generation of forward photonstraveling in a same direction as the electrons and reflected photonstraveling in different directions as the electrons, and facilitateutilization of the forward photons and reflected photons to irradiatesamples positioned in the same direction as the electrons and in thedifferent directions including around the housing of the x-ray tube. 2.The X-ray tube of claim 1, wherein said anode structure is coated withthe target element to produce a bremsstrahlung X-ray from a plurality ofaccelerated electrons originating from said filament.
 3. The X-ray tubeof claim 1, wherein said low Z material of the anode structure issubstantially X-ray transparent.
 4. The X-ray tube of claim 2, whereinsaid target element is formed thereon said anode structure via one ofelectro-chemically platted plating, mechanically bonding, or vapordeposition using evaporation or sputtering technique.
 5. The X-ray tubeof claim 3, wherein said low Z material consists of one or more of thegroup consisting of: Beryllium, Carbon, Aluminum, Ceramic, StainlessSteel, or alloys thereof.
 6. The X-ray tube of claim 2, wherein saidcathode structure produces an electrostatic field that equallydistributes said plurality of accelerated electrons originating fromsaid filament onto said target element formed on said anode structure,wherein a portion of the cathode structure has a flared configurationthat flares outwards and away from a remaining portion of the cathodestructure and towards the housing, wherein the portion of the cathodehaving the flared configuration flares away from the filament.
 7. TheX-ray tube of claim 1, wherein said X-ray tube produces a symmetricalhemispherical shaped X-ray field.
 8. The X-ray tube of claim 1, whereinsaid X-ray tube facilitates the generation of the reflected photonsbased on the electrons contacting the target element deposited on aninner surface of the target anode structure.
 9. The X-ray tube of claim8, wherein a linear distance between said anode structure and saidcathode structure is adjusted to vary a number of the reflected photons.10. The X-ray tube of claim 9, wherein said linear distance is increasedto increase a breadth of a pattern of the reflected photons produced bythe X-ray tube.
 11. The X-ray tube of claim 9, wherein said lineardistance is reduced to reduce a breadth of the pattern of the reflectedphotons produced via the X-ray tube.
 12. The X-ray tube of claim 4,wherein said target element comprises a high Z element.
 13. The X-raytube of claim 4, wherein said X-ray tube produces an output X-rayspectrum determined by the target element and a cathode voltage.
 14. TheX-ray tube of claim 4, wherein said X-ray tube produces an output X-rayspectrum determined by a k alpha energy line of the target element and acathode voltage.
 15. The X-ray tube of claim 12, wherein the targetelement thickness is determined by cathode voltage and a conversionefficiency of the target element.